WO2002005715A1 - Appareil de diagnostic cardiaque a champ magnetique par potentiel ventriculaire tardif et procede de localisation d'une partie de propagation d'excitation intramyocardique inegale - Google Patents

Appareil de diagnostic cardiaque a champ magnetique par potentiel ventriculaire tardif et procede de localisation d'une partie de propagation d'excitation intramyocardique inegale Download PDF

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Publication number
WO2002005715A1
WO2002005715A1 PCT/JP2001/006194 JP0106194W WO0205715A1 WO 2002005715 A1 WO2002005715 A1 WO 2002005715A1 JP 0106194 W JP0106194 W JP 0106194W WO 0205715 A1 WO0205715 A1 WO 0205715A1
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Prior art keywords
myocardium
excitation
magnetic field
data
propagation
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PCT/JP2001/006194
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English (en)
Japanese (ja)
Inventor
Kenji Nakai
Masahito Yoshizawa
Kohei Kawazoe
Keita Yamazaki
Satoshi Fujita
Itsuro Tamura
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Japan Science And Technology Corporation
Takenaka Corporation
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Application filed by Japan Science And Technology Corporation, Takenaka Corporation filed Critical Japan Science And Technology Corporation
Priority to US10/333,056 priority Critical patent/US6941165B2/en
Priority to EP01950019A priority patent/EP1302161A4/fr
Priority to AU2001271070A priority patent/AU2001271070A1/en
Publication of WO2002005715A1 publication Critical patent/WO2002005715A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computed tomography [CT]
    • A61B6/032—Transmission computed tomography [CT]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/242—Detecting biomagnetic fields, e.g. magnetic fields produced by bioelectric currents
    • A61B5/243—Detecting biomagnetic fields, e.g. magnetic fields produced by bioelectric currents specially adapted for magnetocardiographic [MCG] signals
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A61B5/316—Modalities, i.e. specific diagnostic methods
    • A61B5/318—Heart-related electrical modalities, e.g. electrocardiography [ECG]
    • A61B5/346—Analysis of electrocardiograms
    • A61B5/349—Detecting specific parameters of the electrocardiograph cycle
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computed tomography [CT]
    • A61B6/037—Emission tomography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/50—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications
    • A61B6/503—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment specially adapted for specific body parts; specially adapted for specific clinical applications for diagnosis of the heart
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
    • A61B6/5211—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data
    • A61B6/5229—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data combining image data of a patient, e.g. combining a functional image with an anatomical image
    • A61B6/5235—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data combining image data of a patient, e.g. combining a functional image with an anatomical image combining images from the same or different ionising radiation imaging techniques, e.g. PET and CT
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
    • A61B6/5211—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data
    • A61B6/5229—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data combining image data of a patient, e.g. combining a functional image with an anatomical image
    • A61B6/5247—Devices using data or image processing specially adapted for radiation diagnosis involving processing of medical diagnostic data combining image data of a patient, e.g. combining a functional image with an anatomical image combining images from an ionising-radiation diagnostic technique and a non-ionising radiation diagnostic technique, e.g. X-ray and ultrasound
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5215—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data
    • A61B8/5238—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data for combining image data of patient, e.g. merging several images from different acquisition modes into one image
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T19/00—Manipulating 3D models or images for computer graphics
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves 
    • A61B5/055—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves  involving electronic [EMR] or nuclear [NMR] magnetic resonance, e.g. magnetic resonance imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/74—Details of notification to user or communication with user or patient ; user input means
    • A61B5/742—Details of notification to user or communication with user or patient ; user input means using visual displays
    • A61B5/743—Displaying an image simultaneously with additional graphical information, e.g. symbols, charts, function plots

Definitions

  • the present invention relates to an apparatus for diagnosing a cardiac magnetic field of a ventricular delay potential and a method for identifying an uneven propagation site in a myocardium. More specifically, the present invention relates to a ventricular delay potential that causes a ventricular tachycardia, that is, an excitation failure in a myocardium. The present invention relates to a cardiac magnetic field diagnostic apparatus for a ventricular delayed potential for non-invasively diagnosing the three-dimensional occurrence position of a uniform propagation site by non-contact magnetic measurement, and a method of identifying an uneven propagation site in a myocardium.
  • Background art
  • ECG is an indirect measurement method.
  • the tissue existing from the heart to the body surface, the positional relationship between the heart and other organs and bones, the size of the heart, the electrical conductivity of each tissue of the human body, etc. differ greatly from subject to subject. It was extremely difficult to pinpoint the affected part with the information obtained by such indirect measurements.
  • a mottled tissue refers to a state in which dying or degenerated tissues are present in the form of islands in normal myocardial tissue. Non-uniform excitation propagation occurs at such a myocardial site, and a ventricular delayed potential is generated. In addition, in such mottled tissue, there is a double interest due to the difference in electrical conduction characteristics between dead or degenerated tissue and normal tissue. A stray propagation path (reentry circuit) may be formed.
  • the excitement signal turns in the reentry circuit, and as a result, ventricular tachycardia is induced. Therefore, there is a strong demand for accurate identification of the site of occurrence of such a ventricular delayed potential in three dimensions.
  • endocardial mating using a catheter which is an invasive test, is performed, and the site of heterogeneous transmission of intracardiac excitation is identified by observing fragmented activity.
  • an electrophysiological examination using this catheter has been used to identify the heterogeneous propagation site of intramuscular excitement, and to further cauterize the abnormal excitation propagation site with high frequency (catheter ablation method). ing.
  • a QUID Superconducting Quantum Interference Device
  • SQUID magnetic flux using a Superconducting Quantum Interference Device (hereinafter referred to as "", a QUID) that can detect magnetic flux of about 1/1 billion of geomagnetism with high sensitivity Meter is applied in various fields.
  • a QUID Superconducting Quantum Interference Device
  • noncontact magnetic measurement of the human body using an SQUID magnetometer has been attempted.
  • the excitation propagation path from the sinoatrial node to the atrioventricular node, the His bundle and the Purkinje fiber system can be expressed by the signal source estimation method using the above-mentioned current dipole.
  • the method of imitating and visualizing a magnetic field source with one or more current dipoles only obtains the position information of the current dipole at a certain time, and the site where the ventricular delayed potential occurs in the myocardium In other words, it was not possible to identify the position, size, and shape of the site of heterogeneous transmission of myocardial excitation three-dimensionally.
  • an object of the present invention is to provide a portion of the myocardium where a ventricular delayed potential is generated, that is, the excitation of the intramyocardial excitation, based on data indicating the three-dimensional electrical activity state in the myocardium obtained by non-invasive magnetic measurement.
  • An object of the present invention is to provide an apparatus for diagnosing a cardiac magnetic field of a ventricular delayed potential and a method for identifying a non-uniformly transmitted site of a myocardium, which can safely, rapidly and accurately three-dimensionally identify a positional relationship of a non-uniformly transmitted site. Disclosure of the invention
  • a cardiac magnetic field diagnostic device for ventricular delayed potential includes a magnetic field distribution measuring device, a first arithmetic device, a second arithmetic device, and a display device.
  • the magnetic field distribution measuring device acquires a plurality of magnetic field time series data corresponding to a plurality of coordinates by non-contact magnetic measurement at a plurality of coordinates on the subject's chest, and obtains a plurality of magnetic field time series data based on the plurality of magnetic field time series data.
  • the magnetic field distribution time series data is generated.
  • the first arithmetic unit generates data indicating a three-dimensional electrical activity state in the myocardium of the subject based on the generated magnetic field distribution time-series data.
  • the second arithmetic unit processes the separately supplied chest tomographic image data of the subject to generate data indicating an anatomical image.
  • the display device is the first computing device
  • a display process is performed in which an image of a three-dimensional electrical activity state in the myocardium indicated by the generated data is superimposed on an anatomical image indicated by the data generated by the second computing device.
  • the data indicating the three-dimensional electrical activity state in the myocardium generated by the first arithmetic unit is data indicating a propagation speed of excitation in the myocardium.
  • the first arithmetic unit approximates an excitation propagation path site in the myocardium using one or a plurality of minute current elements, and calculates a temporal change in the position of the minute current element. Generates data indicating the speed of propagation of myocardial excitation.
  • the first arithmetic unit generates data indicating a difference in propagation speed of excitation in the myocardium for each excitation propagation path based on the calculated temporal change in the position of the minute current element.
  • a cardiac magnetic field diagnostic device for ventricular delayed potential includes a magnetic field distribution measuring device, a computing device, and a display device.
  • the magnetic field distribution measurement device acquires a plurality of magnetic field time series data corresponding to a plurality of coordinates by non-contact magnetic measurement at a plurality of coordinates on the subject's chest, and obtains a magnetic field on the chest based on the plurality of magnetic field time series data.
  • Generate field distribution time series data Generate field distribution time series data.
  • the arithmetic unit generates data indicating a three-dimensional electrical activity state in the myocardium of the subject based on the generated magnetic field distribution time-series data.
  • the display device Based on the data generated by the computing device, the display device displays images showing the stimulus propagation path from the sinoatrial node of the subject's heart to the Hiskin-Pukkin fiber system, and three-dimensional electrical activity in the myocardium. A display process for superimposing and displaying an image indicating the state is performed. As a result, it is possible to three-dimensionally identify the localization of the ventricular delay potential due to the uneven propagation of the excitation in the myocardium.
  • the data indicating the three-dimensional electrical activity state in the myocardium generated by the arithmetic device is data indicating a propagation speed of excitation in the myocardium.
  • the arithmetic unit approximates the excitation propagation path site in the myocardium using one or a plurality of microcurrent elements, and calculates a temporal change in the position of the microcurrent element, thereby Generate data indicating the speed of propagation of the excitement.
  • the arithmetic unit is configured to change the position of the calculated minute current element over time. Based on the data, data representing the difference in the propagation speed of the excitation in the myocardium for each excitation propagation path is generated.
  • a method for identifying a site of heterogeneous excitation in a myocardium comprises a plurality of magnetic fields corresponding to a plurality of coordinates obtained by a non-contact magnetic measurement at a plurality of coordinates on a chest of a subject.
  • the three-dimensional electrical activity state in the myocardium indicated by the first data is a propagation speed of the excitation in the myocardium.
  • the step of generating the first data includes the step of approximating an excitation propagation path in the myocardium using one or a plurality of minute current elements, and calculating a temporal change in the position of the minute current element. This generates data indicating the propagation speed of excitation in the myocardium. More preferably, the step of generating the first data generates data indicating a difference in propagation speed for each excitation propagation path based on the calculated temporal change in the position of the minute current element.
  • a method for identifying a site of heterogeneous excitation in a myocardium comprises a plurality of magnetic fields corresponding to a plurality of coordinates obtained by a non-contact magnetic measurement at a plurality of coordinates on a chest of a subject.
  • Generating three-dimensional electrical activity in the myocardium of the subject based on the time-series data of the magnetic field distribution on the chest generated based on the serial data; and
  • the excitation in the myocardium becomes uneven.
  • the data indicates that the three-dimensional electrical activity in the myocardium is a transmission Seeding speed.
  • the step of generating data includes: approximating an excitation propagation path site in the myocardium using one or more microcurrent elements, and calculating a temporal change in a position of the microcurrent element.
  • data indicating the propagation speed of the excitation in the myocardium is generated.
  • the data generating step generates data indicating a difference in the propagation speed of the intramyocardial excitation for each excitation propagation path based on the calculated temporal change in the position of the minute current element.
  • an image showing the three-dimensional electrical activity state in the myocardium obtained by non-invasive magnetic measurement is used to convert chest tomographic image data of the same subject taken by another medical diagnostic apparatus.
  • the physician can localize the site of occurrence of ventricular delayed potential that causes ventricular tachycardia, that is, the site of inhomogeneous non-uniform propagation in the myocardium. Can be identified safely, quickly and with high accuracy.
  • the image showing the three-dimensional electrical activity state in the myocardium obtained by non-invasive magnetic measurement is used to stimulate the His bundle-Purkinje fiber system from the sinoatrial node of the heart of the same subject.
  • doctors can safely, promptly, and accurately localize the site of the occurrence of ventricular delayed potential that causes ventricular tachycardia, that is, the site of uneven excitation in the myocardium. It is possible to identify with high accuracy.
  • FIG. 1 is a functional block diagram schematically showing a configuration of a cardiac magnetic field diagnostic apparatus for ventricular delayed potential according to Embodiment 1 of the present invention.
  • FIG. 2 is a block diagram showing a more specific configuration of the cardiac magnetic field diagnostic device shown in FIG.
  • FIG. 3 is a block diagram showing a detailed configuration of the magnetic field distribution measuring device shown in FIG.
  • FIG. 4 is a diagram showing an example of the arrangement of a plurality of magnetic field sensors on the front of the chest of the subject.
  • FIG. 5 is a diagram showing magnetic field time-series data obtained from each of the plurality of sensors in FIG.
  • FIG. 6 is a diagram showing an example of a three-dimensional anatomical image displayed on the display device 4.
  • FIG. 7 is a flowchart illustrating the operation of the cardiac magnetic field diagnostic device according to Embodiment 1 of the present invention.
  • FIG. 8 is a functional block diagram schematically showing a configuration of a ventricular delayed potential cardiac magnetic field diagnostic apparatus according to Embodiment 2 of the present invention.
  • FIG. 9 is a block diagram showing a more specific configuration of the cardiac magnetic field diagnostic device according to the second embodiment of the present invention shown in FIG.
  • FIGS. 1OA and 10B are diagrams schematically showing a normal stimulus propagation path and an electrocardiogram waveform in the heart.
  • FIG. 11 is a diagram showing images of the normal stimulus propagation path and the excitation propagation path actually displayed by the display device 6.
  • FIG. 12 is a flowchart illustrating the first half of the operation of the cardiac magnetic field diagnostic device according to the second embodiment.
  • FIG. 13 is a flowchart illustrating the latter half of the operation of the cardiac magnetic field diagnostic device according to the second embodiment.
  • FIG. 1 is a functional block diagram schematically showing a configuration of a cardiac magnetic field diagnostic apparatus for ventricular delayed potential according to Embodiment 1 of the present invention.
  • the magnetic field distribution measurement device 1 performs non-contact magnetic measurement at a plurality of coordinates on a subject's chest using, for example, measurement means such as an S QU ID magnetometer described in detail below. Acquire a plurality of magnetic field time-series data corresponding to a plurality of coordinates. Then, based on the plurality of acquired magnetic field time-series data, the time-series data on the chest, that is, the magnetic field distribution of the cardiac magnetic field is generated and output.
  • measurement means such as an S QU ID magnetometer described in detail below.
  • the first arithmetic device 2 Based on the time-series data of the magnetic field distribution of the heart measured by the magnetic field distribution measuring device 1, the first arithmetic device 2 uses a well-known calculation method to be described later to generate a three-dimensional Generating and outputting first data indicating a mood activity state.
  • the first arithmetic unit 2 generates data indicating the propagation speed of excitation in the myocardium.
  • this propagation velocity is calculated by approximating the site of the excitation propagation path in the myocardium using one or a plurality of minute current elements, that is, current dipoles, and calculating the temporal change in the position of the current dipole. Is obtained by Based on the temporal change of the obtained current dipole, data on the propagation velocity for each excitation propagation path can be obtained. As a result, it is possible to specify the localization of the ventricular delay potential caused by the uneven propagation of the window.
  • tomographic image data of the same subject's chest obtained separately by tomographic diagnostic equipment such as nuclear magnetic resonance (MR I), X-ray CT, echocardiography, and myocardial SPECT 1
  • tomographic diagnostic equipment such as nuclear magnetic resonance (MR I), X-ray CT, echocardiography, and myocardial SPECT 1
  • MR I nuclear magnetic resonance
  • X-ray CT X-ray CT
  • echocardiography X-ray CT
  • myocardial SPECT 1 myocardial SPECT
  • the electrical activity state obtained by the first arithmetic unit 2 is the propagation speed of the excitation in the myocardium, it is displayed on the screen in some form.
  • the nonuniformity of the propagation velocity of the excitation in the myocardium for each excitation propagation path it is possible to identify the location of the occurrence of the ventricular delay potential in three dimensions.
  • the display device 4 displays an image showing the three-dimensional electrical activity in the myocardium (for example, the propagation velocity for each excitation propagation path) indicated by the first data generated by the first arithmetic device,
  • the 3D anatomical image of the subject's chest indicated by the second data generated by 3 is superimposed and displayed.
  • FIG. 2 is a block diagram more specifically showing the configuration of the cardiac magnetic field diagnostic apparatus for ventricular delayed potential according to the first embodiment of the present invention shown in FIG.
  • the magnetic field distribution measuring device 1 has a magnetic shield room (Magnetic
  • MSR Shield Room
  • a unit 13 with a built-in SQUID magnetometer installed to perform non-contact magnetic measurement on the chest of the subject 12, and a calculation unit for magnetic field distribution data 1 and 4 are provided.
  • the SQUID magnetometer which consists of a superconducting detection coil, is housed inside.
  • Fig. 3 shows the SQUID magnetometer 15 installed in the ultra low temperature system in the dewar 13 in the MSR 11 shown in Fig. 2 and the operation unit 14 installed in the MSR 11 in the normal temperature system in more detail. It is a block diagram shown in FIG.
  • the configuration shown in Fig. 3 is a configuration for one channel for measuring magnetic field data at one point on the chest of the subject. As will be described later, in the present invention, multipoint simultaneous measurement of a magnetic field at a plurality of coordinates is performed on the chest of a subject. Therefore, the configuration for one channel shown in FIG. 3 is provided in the MSR 11 of FIG. 2 for a plurality of channels required for measurement.
  • the SQUID magnetometer 15 includes a pickup coil 16 made of a superconductor for detecting a magnetic field generated from the chest surface of the subject.
  • a current flows, and this current is drawn into the coil 17 to generate a magnetic field in the Nb shield 20.
  • a magnetic field that changes linearly with respect to this magnetic field is formed in the superconducting loop 18, and the voltage at both ends of the superconducting loop 18 is calculated by the arithmetic unit 14 installed in the normal temperature MSR 11.
  • the arithmetic unit 14 detects the current by the amplifier and adjusts the current flowing through the modulation coil 19 in the Nb shield 20 so that the detected voltage does not change.
  • the detection of the magnetic field of the living body by SQUID does not directly measure the generated magnetic field, but applies feedback so that the magnetic field in the superconducting ring 18 always has a constant value using the so-called zero-position method.
  • the arithmetic unit 14 converts the magnetic field detected by the pickup coil 16 into an electric signal and outputs the electric signal.
  • Such a feedback method is generally known as a “fl ux locked loop (FLL)”.
  • the configuration shown in Fig. 3 is necessary for measuring the magnetic field data for one channel, and the electrical signal indicating the magnetic field time-series data of the magnetic field measured at one point on the front of the subject's chest Is output.
  • many sensors SQUID magnetometer
  • the magnetic field on the front of the chest is measured at multiple points.
  • the magnetic field changes with time. For example, even during a period corresponding to one heartbeat, if the measurement location is different, the magnetic field changes differently depending on the location.
  • FIG. 4 is a diagram showing an example of the arrangement of a plurality of sensors (each of which is a single channel SQUID magnetometer) on the front of the chest of the subject.
  • FIG. 5 shows a group of magnetic field time-series data showing a change in a magnetic field during one heartbeat period obtained from each sensor corresponding to each position of the plurality of sensors in FIG. I have.
  • the data output from the magnetic field distribution measuring device 1 shown in FIG. 2 is a group of magnetic field time series data corresponding to a plurality of measurement positions (coordinates) as shown in FIG. 5, but attention is paid to a specific time Then, when these one group of magnetic field time series data is captured, a graph (figure) is used to represent the actual state of the peaks and valleys showing the distribution of the magnetic field strength at a certain time on the front of the chest to be measured. Because it is difficult to obtain, the magnetic field distribution data expressed by a contour map like the atmospheric pressure of the weather chart can be obtained. For this reason, the data output from the magnetic field distribution measuring device 1 can be regarded as magnetic field distribution time-series data on the front of the chest.
  • Such a group of magnetic field time-series data that is, magnetic field distribution time-series data output from the magnetic field distribution measuring device 1 is given to the first arithmetic device 2 in FIG.
  • the first arithmetic unit 2 functions to determine the electrical activity in the chest, for example, the propagation speed of excitation in the myocardium based on the magnetic field distribution data.
  • the first arithmetic unit 2 uses the magnetic field distribution time series data generated by the magnetic field distribution measuring device 1 to obtain information on three-dimensional electrical activity at a site in the human body (the heart in the present invention) to be measured. , For example, a method to determine the propagation speed of intracardiac excitation I will tell.
  • the first arithmetic unit 2 approximates the magnetic field distribution time-series data generated by the magnetic field distribution measuring device 1 using one or a plurality of minute current elements (that is, current dipoles). That is, the above minute current elements are scattered in the measured cardiac magnetic field distribution, and parameters (positional information and current vector) of each minute current element corresponding to each measurement point are determined by a well-known analysis method. I do.
  • the analysis method using such a current dipole is a well-known method, for example, as disclosed in detail in Japanese Patent Application Laid-Open No. 5-157735, and a detailed description thereof is omitted here. .
  • the first arithmetic unit 2 first generates data indicating such a change over time in the position of the minute current element and the direction of the current, and supplies the data to one input of the display device 4. Further, the first arithmetic unit 2 may calculate the propagation speed of the excitation in the myocardium based on the above-mentioned temporal change, and may generate the result as numerical data.
  • the image data may be generated as image data to be visually displayed based on the length of the arrow.
  • the first arithmetic unit 2 generates, from the magnetic field distribution data generated by the magnetic field distribution measuring device 1, various types of time-series data indicating the propagation speed of the excitation in the myocardium to be analyzed, and displays the data. Applied to one input of device 4.
  • the second arithmetic unit 3 shown in FIG. 2 is provided with an electrocardiogram synchronization trigger in advance by using another tomography diagnostic device (not shown), for example, an MR I method, an X-ray CT method, an echocardiogram method, a myocardial SPECT method, or the like.
  • Image data of a plurality of slice images (for example, about a dozen or so images at 5 mm pitch) of the same subject's chest photographed with the camera is input.
  • the second arithmetic unit 3 processes (interpolates) the data of the plurality of slice images, performs three-dimensional perspective transformation from a predetermined viewpoint, and generates second data indicating an anatomical image.
  • Techniques for forming a three-dimensional anatomical image from a plurality of slice images in this manner are well known. For example, Japanese Patent Application Laid-Open No. H11-12828, International Publication W ⁇ 98 / 15 It is disclosed in detail in Japanese Patent Publication No. So the details here I will not explain it.
  • the second arithmetic unit 3 generates second data indicating a three-dimensional anatomical image of the chest near the heart of the same subject, and supplies the second data to the other input of the display device 4.
  • the display device 4 shown in FIG. 2 displays the three-dimensional anatomical image of the subject's chest formed based on the second data from the second arithmetic device 3 on the three-dimensional anatomical image from the first arithmetic device 2. Images showing the time-dependent changes in the position and direction of the current in the myocardium formed based on the data of step 1 are displayed in a superimposed manner.
  • FIG. 6 shows the position and direction of the microcurrent element representing the excitation current in the myocardium in the cardiac magnetic field distribution at a certain time, superimposed on the three-dimensional anatomical image displayed by the display device4, and
  • FIG. 7 is a diagram showing a form in which an excitement propagation path up to the time is displayed.
  • Figure 6 shows a three-dimensional image obtained by interpolating about five tomographic images obtained by slicing the subject's chest at a 5 mm pitch, for example. Although it is difficult to express the sense of depth of the actual display image on the drawing, it is assumed that the image shows a three-dimensional anatomical image with a sense of depth formed by combining a plurality of slice images.
  • the arrow indicated by ⁇ indicates the position and direction of the microcurrent element representing the excitation current in the myocardium at that time, and the length of the arrow indicates the magnitude of the current.
  • the thick lines B, C, and D indicate the trajectories of the excitation propagation paths in the myocardium obtained by approximating the cardiac magnetic field by the minute current element until the time. The change of the position of the minute current element is connected over time.
  • the locus of the minute current element at the current position becomes dense, and conversely, at a site where the propagation speed is high, the position of the minute current element at the current position is small Is coarse. Therefore, it is possible to visually recognize the propagation speed of each intramyocardial excitation based on the density of the minute current element constituting each of the thick lines B, C, and D indicating the excitation propagation path displayed on the screen. It is possible.
  • the propagation speed itself of the excitation in the myocardium may be calculated by the first arithmetic device 2 and displayed on the display device 4 as a number.
  • the physician can accurately grasp the location of the ventricular delayed potential in the myocardium, that is, the relative position of the heterogeneous propagation of the excitation in the myocardium on the anatomical image by displaying the can do.
  • FIG. 7 is a flowchart showing a method of identifying a site of non-uniform propagation of excitation in the myocardium performed by the cardiac magnetic field diagnostic device according to Embodiment 1 described above.
  • step S1 non-contact magnetic measurement is performed at a plurality of coordinates on the human chest by the magnetic field distribution measuring device 1, and a plurality of time-series data is generated, and recorded if necessary.
  • step S2 an interpolation operation (three-dimensional perspective transformation from a predetermined viewpoint) is performed by the second arithmetic unit 3 on the plurality of MRI images photographed in advance with the ECG synchronization trigger, and the three-dimensional Obtain an anatomical image of.
  • step S3 the initial time of the analysis is set to t s , the end time of the analysis is set to t e , and the time interval of the analysis is set to ⁇ t.
  • step S4 the analysis is started by substituting the initial time t s for the analysis time t. Then, in step S5, the following loop-like processing is repeatedly performed until the analysis time t reaches the end time t e .
  • step S6 the first arithmetic unit 2 approximates the cardiac magnetic field distribution data at the designated analysis time t with one or a plurality of minute current elements to obtain the position, direction, and magnitude of the excitation current in the myocardium. Get data about
  • step 7 the step of the previous loop preceding by time ⁇ t
  • the data on the position, direction, and magnitude of the excitation current in the myocardium at time t— ⁇ t obtained in S6 are compared with the data at time t obtained in step S6 this time. Calculate the propagation speed of the excitement.
  • step S8 the display device 4 superimposes and displays the data indicating the propagation speed of the excitation in the myocardium from a predetermined viewpoint to an anatomical image subjected to three-dimensional perspective transformation.
  • step S9 ⁇ t is added to the analysis time t.
  • a three-dimensional image showing the propagation speed of intramyocardial excitation obtained by noninvasive magnetic measurement on the subject's chest using the SQUID magnetometer By superimposing on the anatomical image, the anatomical positional relationship, size, and shape of the site of occurrence of ventricular delayed potential in the myocardium that causes ventricular tachycardia, that is, the site of heterogeneous propagation of excitation in the myocardium, can be displayed. Doctors can be identified three-dimensionally.
  • the second embodiment of the present invention provides a cardiac magnetic field diagnostic apparatus for a ventricular delayed potential, which can reduce the number of examinations and can perform diagnosis and examination directly by eliminating the need for forming an anatomical image.
  • An object of the present invention is to provide a method for identifying a site of heterogeneous transmission of myocardial excitation.
  • FIG. 8 is a functional block diagram schematically showing a configuration of a cardiac magnetic field diagnostic apparatus for ventricular delayed potential according to Embodiment 2 of the present invention.
  • magnetic field distribution measuring apparatus 1 has already been described in relation to Embodiment 1, and will not be described again here.
  • the arithmetic unit 5 calculates the three-dimensional electrical activity state in the myocardium, for example, data on the excitation current in the myocardium, using the analysis method using the current dipole described above based on the given magnetic field distribution time-series data. Generate. Then, based on the generated data on the excitatory current, the arithmetic unit 5 calculates, from the P wave of the electrocardiogram, data indicating an excitement (stimulus) propagation path in the myocardium of the ventricle during a period corresponding to the QRS group, It is generated by superimposing data indicating the propagation speed on the display device 6.
  • the display device 6 displays an image showing the propagation speed of the intramyocardial excitation indicated by the data generated by the arithmetic unit 5 and the excitation propagation path corresponding to the period of the QRS group from the P wave of the electrocardiogram similarly obtained by the arithmetic unit 5. It is superimposed on a 3D image and displayed. As a result, it is possible to three-dimensionally identify the positional relationship between the sites of uneven propagation of myocardial excitation without using an anatomical image as in the first embodiment.
  • FIG. 9 is a block diagram more specifically showing the configuration of the cardiac magnetic field diagnostic apparatus for ventricular delayed potential according to the second embodiment of the present invention shown in FIG.
  • magnetic field distribution measuring device 1 is the same as magnetic field distribution measuring device 1 described with reference to FIGS. 2 and 3, and therefore description thereof is omitted here.
  • the magnetic field distribution time-series data output from the magnetic field distribution measuring device 1 is given to the arithmetic device 5 in FIG. 9, and the arithmetic device 5 performs the magnetic field distribution time-series data by the above-described analysis method using the current dipole. Then, data on the excitation current in the myocardium is generated.
  • an electrocardiograph 21 for recording the electrocardiogram of the subject 12 is provided, and the electrocardiogram waveform data of the subject 12 measured by this is supplied to the arithmetic unit 5.
  • FIG. 10A is a diagram schematically showing a normal stimulus propagation path in the heart
  • FIG. 10B shows an electrocardiogram waveform for one heartbeat.
  • the sinoatrial node of the heart functions as a pacemaker that determines the heart rate, and fires at regular intervals (the timing of the P wave of the electrocardiogram) to generate a pulse.
  • This pulse travels to the atrioventricular node via a predetermined stimulus propagation path, where after a certain time delay, the pulse is transmitted from the His (bundle) bundle to the lower ventricle via the pu / kine fiber system.
  • the pulse is transmitted from the His (bundle) bundle to the lower ventricle via the pu / kine fiber system.
  • contraction of the heart muscle occurs at a stretch. Pull from this His bundle
  • the propagation of the stimulus of the Kinje fiber system corresponds to the duration of the QRS complex on the ECG.
  • the arithmetic unit 5 indicates the stimulus propagation path as a normal note as shown in FIG. 10A. Generate image data.
  • Such an image of the stimulus propagation path shown in FIG. 10A can be used as a template display instead of the anatomical image of the first embodiment. That is, even if there is no three-dimensional anatomical image as in Embodiment 1, if the stimulus propagation path of the normal route shown in FIG. 10A is displayed, the ventricle generated in the surrounding ventricle is displayed.
  • a physician can easily make anatomical correspondences to the delayed potential site, that is, the site of non-uniform transmission of excitation in the myocardium, and can identify its position, size, and shape.
  • the arithmetic unit 5 in FIG. 9 generates data indicating the generated propagation speed of the intramyocardial excitation, superimposed on the display of the stimulus propagation path as such a template.
  • data indicating the generated propagation speed of the intramyocardial excitation, superimposed on the display of the stimulus propagation path as such a template.
  • the display device 6 shown in FIG. 9 displays an image showing the propagation speed of myocardial excitation, based on the data from the arithmetic device 5 and superimposed on a normal stimulus propagation path as a template. Thereby, the doctor can easily determine whether or not the reentry circuit is easily formed in the ventricular muscle.
  • Fig. 11 shows an example of a screen actually displayed by the display device 6, in which images showing the propagation speed of myocardial excitation for each excitation propagation path are displayed, superimposed on the normal stimulation propagation path as a template. Have been.
  • each of the two arrows indicates the position of the excitation propagation path approximated by a minute current element (current dipole).
  • the length of each arrow indicates the speed of the excitation propagation speed. I have.
  • a physician can easily make an anatomical correspondence based on the relative positional relationship of each excitation propagation path to the normal stimulation propagation path as a template shown in FIG. In addition, based on the difference in propagation speed between each It is possible to identify the location, size, and shape of the site of ventricular delayed potential generation in the ventricle, that is, the site of heterogeneous propagation of excitation in the myocardium.
  • FIGS. 12 and 13 are flowcharts showing a method of identifying a site of non-uniform propagation of excitation in the myocardium, which is performed by the diagnostic apparatus for ventricular delayed potential according to the second embodiment.
  • step S 11 non-contact magnetic measurement is performed at a plurality of coordinates on the human chest using the magnetic field distribution measuring device 1 to generate and record a plurality of magnetic field time series data. I do.
  • step S12 the initial time of the analysis is defined as the P wave start time t of the ECG, the analysis end time is defined as the QRS group end time t eQRS of the ECG, and the analysis time interval is defined as ⁇ .
  • step S13 t sP which is the start time of the P wave is substituted for the analysis time t.
  • step S14 the following steps S15 to S17 are repeated until the analysis time reaches the end time teQRS .
  • step S15 the arithmetic unit 5 approximates the cardiac magnetic field distribution data at the designated analysis time t with one or a plurality of minute current elements, and calculates the position, direction, and magnitude of the exciting current in the myocardium. Get data about
  • step S16 an image obtained by performing a three-dimensional perspective transformation on the data of the excitation current in the myocardium obtained in step S15 from a predetermined viewpoint is displayed.
  • step S17 ⁇ t is added to the analysis time t, and the process returns to step S14 to determine whether the end time t eQRS has been reached. If it is determined that the end time t eQRS has been reached, the image data showing the stimulus propagation path, which is the normal route shown in Fig. 1 OA, is associated with the period corresponding to the QRS group from the P wave in the ECG waveform. Is obtained.
  • step S 1 8 in FIG. 1 3 it defines the initial time of the angular family loaf and t s, defined as the end time and t e corner ⁇ , defined as delta t the analysis time interval.
  • step S19 the initial time t s is substituted for the analysis time t.
  • step S 2 until the analysis time t is determined that it has reached the end time t e, the following steps S 2 1 to S 2 4 is executed in a loop. That is, in step S21, the arithmetic unit 5 approximates the cardiac magnetic field distribution data at the specified analysis time t with one or a plurality of minute current elements, and calculates the position, direction, and magnitude of the exciting current in the myocardium. Get data about
  • step S22 data on the position, direction, and magnitude of the excitation current in the myocardium at time t- ⁇ t obtained in step S21 of the previous loop preceding by time ⁇ t, By comparing with the data at time t obtained in step S21, the propagation speed of the excitation in the myocardium is calculated.
  • step S23 the display device 6 superimposes and displays the data representing the propagation velocity of the excitation in the myocardium on the image of the normal stimulus propagation circuit subjected to three-dimensional perspective transformation from a predetermined viewpoint.
  • step S24 ⁇ t is added to the analysis time t, and the process returns to step S20 to determine whether the end time t e has been reached.
  • the data indicating the propagation rate of the excitation in the myocardium is superimposed and displayed on the image of the stimulus propagation path (FIG. 10A) obtained in the flow chart of FIG.
  • an image showing the propagation velocity of intramyocardial excitation obtained by noninvasive magnetic measurement on the subject's chest using the S QU ID magnetometer is By superimposing on the normal stimulus propagation path as a template, the site of occurrence of ventricular delayed potential in the myocardium that causes ventricular tachycardia, that is, in the myocardium, without superimposing on other anatomical images It enables doctors to identify the relative positional relationship, size, and shape of the unequally distributed excitement site with respect to the stimulus propagation path in three dimensions. Therefore, in the second embodiment, a prior examination for obtaining an anatomical image can be omitted.
  • the excitation propagation path using the current dipole is approximated to generate image data of the normal stimulation propagation path as a template display. This image can be obtained by the arithmetic unit 5 calculating the current density distribution in the myocardium from the magnetic field distribution time-series data generated by the magnetic field distribution measuring device 1.
  • the following methods can be used to determine the current density distribution in the myocardium. That is, various methods such as SAM (Synthetic Aperture Magnetometry) or MU SIC (Multiple Signal Classification) can be used.
  • SAM Synthetic Aperture Magnetometry
  • MU SIC Multiple Signal Classification
  • SAM and MU SIC have been researched and developed in fields such as radar and sonar, and their methods are well known, but they have not yet been applied to the diagnosis of cardiac magnetic fields. Absent.
  • the present invention it is possible to visually display, on a three-dimensional anatomical image, the propagation speed of intramyocardial excitation obtained by noninvasive magnetic measurement on the chest of a patient. Because of this, it is possible to three-dimensionally identify the location, size, and shape of the site where the ventricular delayed potential is generated, that is, the site of heterogeneous transmission of myocardial excitation. Therefore, it is possible to non-invasively diagnose a site of nonuniform propagation of myocardial excitation or a site of generation of a ventricular delayed potential, which causes ventricular tachycardia, thereby enabling a quick and safe examination without imposing a burden on the patient.
  • the target area for electrophysiological examination can be significantly narrowed in advance, and the effect of significantly reducing the amount of X-ray exposure to doctors and radiologists can be achieved. To play.
  • the anatomy is displayed by superimposing the propagation speed of intramyocardial excitation on the normal stimulus propagation path from the sinoatrial node of the same subject to the His bundle-Punole kinje fiber system, and displaying the three-dimensional display. It is possible to three-dimensionally identify the location of the site of heterogeneous transmission of myocardial excitability, that is, the localization and spread of ventricular delayed potentials, without obtaining a target image. In addition, an examination for obtaining an anatomical image can be omitted, and an effect that a more economically efficient diagnosis can be performed can be achieved.
  • the cardiac magnetic field diagnostic apparatus for ventricular delayed potential and the method for identifying a non-uniformly transmitted region of myocardial excitation according to the present invention, the position, size, and shape of the non-uniformly transmitted region of excitation in the myocardium are three-dimensional. This is useful for non-invasive diagnosis of the site of heterogeneous propagation of cardiac muscle excitation or ventricular delayed potential, which causes ventricular tachycardia.

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Abstract

L'invention concerne un dispositif (1) de mesure de distribution de champ magnétique servant à réunir des données chronologiquesde distribution de champ magnétique par mesure magnétique sans contact de plusieurs points de coordonnées sur le sein d'un sujet. En réponse, un premier dispositif (2) d'exploitation génère des données d'image représentant la vitesse de propagation d'une excitation intramyocardique. Un second dispositif (3) d'exploitation génère des données d'image anatomique par traitement de plusieurs éléments de données tomographiques obtenues séparément à l'aide d'un appareil de diagnostic tomographique. A la réception des données, un dispositif (4) d'affichage affiche une image représentant le courant d'excitation intramyocardique sur l'image anatomique. Il est ainsi possible d'identifier facilement la position anatomique d'un potentiel tardif myocardique, s'il en est, dans le muscle cardiaque. En variante, l'image anatomique peut être remplacée par une image montrant comme modèle une trajectoire de propagation de stimulation normale.
PCT/JP2001/006194 2000-07-18 2001-07-17 Appareil de diagnostic cardiaque a champ magnetique par potentiel ventriculaire tardif et procede de localisation d'une partie de propagation d'excitation intramyocardique inegale WO2002005715A1 (fr)

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US10/333,056 US6941165B2 (en) 2000-07-18 2001-07-17 Cardiac magnetic field diagnosing apparatus by late ventricular potential and method of locating intramyocardial excitement uneven propagation portion
EP01950019A EP1302161A4 (fr) 2000-07-18 2001-07-17 Appareil de diagnostic cardiaque a champ magnetique par potentiel ventriculaire tardif et procede de localisation d'une partie de propagation d'excitation intramyocardique inegale
AU2001271070A AU2001271070A1 (en) 2000-07-18 2001-07-17 Cardiac magnetic field diagnosing apparatus by late ventricular potential and method of locating intramyocardial excitement uneven propagation portion

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JP3712349B2 (ja) * 2000-07-18 2005-11-02 独立行政法人科学技術振興機構 生存心筋診断装置およびその作動方法
JP4027867B2 (ja) * 2003-09-10 2007-12-26 株式会社日立ハイテクノロジーズ 生体磁場計測装置
US9585600B2 (en) 2012-10-02 2017-03-07 Covidien Lp Magnetic field viewing film for tracking in-situ surgical applications
JP6399852B2 (ja) * 2014-08-07 2018-10-03 フクダ電子株式会社 脈波測定装置及び生体情報測定装置
WO2018168864A1 (fr) * 2017-03-17 2018-09-20 Ricoh Company, Ltd. Appareil de traitement d'informations, procédé de traitement d'informations, programme, et système de mesure de signal biologique
CN113317793B (zh) * 2021-06-11 2023-02-17 宁波大学 心磁高频信号分析方法、存储介质及电子设备

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